Implantable dielectrometer

ABSTRACT

Diagnostic apparatus ( 24 ) includes a sealed case ( 80 ), comprising a biocompatible material and configured for implantation within a body of a human subject ( 22 ). A dielectrometric probe ( 26, 50, 63, 66, 70, 102, 160 ) is connected to the case and includes first and second conductors ( 40, 42, 54, 56, 64, 67, 68, 72, 74, 162, 164 ), which are configured to be placed in proximity to a target tissue ( 34 ) in the body. A driving circuit ( 82 ), which is contained in the case, is coupled to apply a radio-frequency (RF) signal to the probe and to sense the signal returned from the probe. Processing circuitry ( 84 ) is configured to evaluate, responsively to the returned signal, a dielectric property of the target tissue.

CROSS-REFERENCE TO RELATED APPLICATION

This application is a continuation of U.S. patent application Ser. No.13/811,217, filed Mar. 28, 2013, titled “Implantable Dielectrometer,”which in turn is a 35 U.S.C. 371 national stage entry ofPCT/IB2011/053246, which has an international filing date of Jul. 21,2011 and entitled “Implantable Dielectrometer,” and claims the benefitof U.S. Provisional Patent Application 61/366,173, filed Jul. 21, 2010.The present application incorporates herein by reference the disclosureof each of the above-referenced applications in their entireties.

FIELD OF THE INVENTION

The present invention relates generally to methods and systems formedical diagnostic measurement and monitoring, and specifically tomeasuring dielectric properties of physiological tissue.

BACKGROUND OF THE INVENTION

The permittivity ∈ of a physical medium is the relationship between theelectric displacement field D and the electric field E in the material:D=∈E. The permittivity of a homogeneous material is commonly expressedrelative to the permittivity of free space, ∈₀, in terms of the relativepermittivity, ∈_(r), defined by s=∈₀∈_(r). The relative permittivity isalso referred to as the “dielectric constant” of the material. Thepermittivity of a lossy material (such as physiological tissue) can bedefined as a complex, frequency-dependent function:

${\hat{ɛ} = {{ɛ^{\prime} - {j\; ɛ^{''}}} = {ɛ^{\prime} - {j\frac{\sigma}{\omega\; ɛ_{0}}}}}},$wherein ∈′ is the real part of the permittivity, σ is the conductivityof the material, and ω is the frequency, while ∈₀ is the free spacepermittivity.

Dielectrometers are used to measure dielectric properties, such as thepermittivity, of materials. For example, U.S. Pat. No. 7,479,790describes a capacitive plate dielectrometer, in which a small sample ofa test material is inserted inside a capacitor for measurement of itsdielectric properties. As another example, U.S. Pat. No. 7,868,627describes a method for measuring dielectric characteristic of materialby irradiating the material with a microwave signal and detecting thereflected signal.

SUMMARY

Embodiments of the present invention that are described hereinbelowprovide implantable devices for measuring dielectric properties of bodytissues. These devices are useful, inter alia, in monitoring fluidlevels within body organs.

There is therefore provided, in accordance with an embodiment of thepresent invention, diagnostic apparatus, which include a sealed case,including a biocompatible material and configured for implantationwithin a body of a human subject. A dielectrometric probe is connectedto the case and includes first and second conductors, which areconfigured to be placed in proximity to a target tissue in the body. Adriving circuit is contained in the case and is coupled to apply aradio-frequency (RF) signal to the probe and to sense the signalreturned from the probe. Processing circuitry is configured to evaluate,responsively to the returned signal, a dielectric property of the targettissue.

Typically, the driving circuit is configured to apply the RF signal tothe probe and to sense the returned signal at multiple differentfrequencies.

In some embodiments, the dielectric property evaluated by the processingcircuitry includes a complex permittivity of the target tissue. Theprocessing circuitry may be configured to evaluate the complexpermittivity by measuring an impedance between the first and secondconductors. Alternatively or additionally, the processing circuitry maybe configured to evaluate the complex permittivity by measuring areflection of the signal from the probe, which is indicative of animpedance mismatch at the target tissue. Further alternatively oradditionally, the processing circuitry may be configured to evaluate thecomplex permittivity by measuring a delay of the signal transmittedthrough the probe. In one embodiment, the processing circuitry isconfigured to evaluate the complex permittivity by measuring a resonantfrequency of the probe.

In a disclosed embodiment, the conductors are arranged to provide acoaxial contact to the target tissue at a distal end of the probe. Thecoaxial contact may include a patch, which is configured to be placedagainst the target tissue. Alternatively, the coaxial contact mayinclude a coaxial tip, in which the first conductor is concentricallycontained within the second conductor, wherein the tip is configured forinsertion into the target tissue.

In other embodiments, the conductors are arranged to define atransmission line in proximity to the target tissue. The transmissionline may be defined by arranging the first conductor as a ground planeand the second conductor as a microstrip parallel to the ground plane.Alternatively, the transmission line may be defined by arranging thefirst and second conductors as parallel lines. Further alternatively,the transmission line may include a coplanar waveguide.

In another embodiment, the conductors are arranged to define a resonantring in proximity to the target tissue.

In some embodiments, the processing circuitry is configured to derive ameasure of a fluid content of the target tissue from the dielectricproperty. The processing circuitry may be configured to measure thefluid content continuously or intermittently, and may be configured tomeasure changes in the fluid content over time.

In disclosed embodiments, the case is configured for implantation in athorax of the subject, and the target tissue includes a lung of thesubject. The probe may be configured for insertion between a rib cageand pleura of the subject and may be configured to bend freely in onedirection, while resisting bending in any other direction. The case maybe configured for insertion between a pair of ribs of the subject.

In some of these embodiments, the apparatus includes a tool configuredto be inserted between ribs of the subject and to guide insertion of theprobe into the rib cage. The tool may include an optical channel, whichis configured to be placed alongside the probe during the insertion ofthe probe into the rib cage and to enable an operator of the tool toview an area into which the probe is to be inserted.

In alternative embodiments, the target tissue is spleen, liver, tongueor palate tissue.

In a disclosed embodiment, at least a part of the processing circuitryis contained in the case and is configured to convey information via awireless link to a telemetry station outside the body. Alternatively oradditionally, the processing circuitry is configured to communicate withat least one other implanted device.

In some embodiments, the apparatus includes a power antenna, which isconfigured to receive electrical energy to power the processingcircuitry via an inductive link from a transmitter outside the body.

The apparatus may further include one or more additional sensors, whichare connected to the case and are configured for implantation in thebody. At least one of the additional sensors may include an electrode,which is configured to receive electrical signals from the heart,wherein the processing circuitry is configured to gate a measurement ofthe returned signal responsively to the electrical signals from theheart.

Additionally or alternatively, the processing circuitry may beconfigured to detect a modulation of the dielectric property due to atleast one of a heartbeat and a respiratory motion of the subject.

There is also provided, in accordance with an embodiment of the presentinvention, a diagnostic method, which includes implanting adielectrometric probe, including first and second conductors, inproximity to a target tissue in a body of a human subject. Aradio-frequency (RF) signal is applied to the probe, and a dielectricproperty of the target tissue is evaluated responsively to the signalreturned from the probe.

The present invention will be more fully understood from the followingdetailed description of the embodiments thereof, taken together with thedrawings in which:

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a schematic pictorial illustration showing a monitoring systemincluding an implanted dielectrometric monitoring device, in accordancewith an embodiment of the invention;

FIG. 2 is a schematic pictorial view of a dielectrometric probe, inaccordance with an embodiment of the invention;

FIG. 3 is a schematic pictorial view of a dielectrometric probe, inaccordance with another embodiment of the invention;

FIG. 4A is a schematic sectional view of the probe of FIG. 3, showinglines of an electric field generated by the probe, in accordance with anembodiment of the invention;

FIGS. 4B and 4C are schematic pictorial views of dielectrometric probes,in accordance with alternative embodiments of the present invention;

FIG. 5 is a schematic side view of a dielectrometric probe, inaccordance with yet another embodiment of the invention;

FIG. 6 is a block diagram that schematically shows functional componentsof a dielectrometric monitoring device, in accordance with an embodimentof the invention;

FIG. 7A is a plot showing the relationship between tissue permittivityand signal delay measured by a dielectrometric monitoring device, inaccordance with an embodiment of the invention;

FIG. 7B is a plot of the complex permittivity of lung tissue as afunction of frequency, in accordance with an embodiment of the presentinvention;

FIG. 8 is a schematic, sectional view through the thorax of a humansubject, showing implantation of a dielectrometric monitoring device inthe thorax, in accordance with an embodiment of the invention;

FIG. 9 is a schematic, sectional view through the thorax of a humansubject, showing implantation of a dielectrometric monitoring device inthe thorax, in accordance with another embodiment of the invention;

FIG. 10 is a schematic pictorial illustration of a surgical tool for usein implantation of a dielectrometric probe, in accordance with anembodiment of the present invention;

FIG. 11 is a schematic pictorial illustration showing a dielectrometricprobe and a surgical accessory for use in implantation of the probe, inaccordance with an embodiment of the present invention;

FIG. 12 is a schematic top view of a dielectrometric probe, inaccordance with a further embodiment of the present invention; and

FIG. 13 is a plot showing the frequency response of the probe of FIG. 12for different values of tissue permittivity, in accordance with anembodiment of the present invention.

DETAILED DESCRIPTION OF EMBODIMENTS Overview

A number of chronic medical conditions lead to accumulation of fluid inand around body organs. One such condition is pulmonary edema, which isassociated with chronic heart failure and other pathologies. Otherconditions can lead to fluid accumulation in other organs, such as theliver, spleen, tongue, palate, and splanchnic system. Monitoring fluidlevels in the patient's body over extended periods can be helpful inongoing risk assessment and adjustment of treatment.

The dielectric properties of body tissues vary due to changes inphysiological conditions and are particularly sensitive to fluidaccumulation in the tissues. For example, the relative permittivity ofnormal lung tissue (in the UHF frequency range) varies from 20 to 40between inhalation and exhalation. In pulmonary edema, however, therelative permittivity increases due to water content in the lungs, andmay reach 75 in serious cases. Thus, monitoring the dielectricproperties of body tissues can provide a useful diagnostic indicatorwith respect to pulmonary edema and other conditions that are associatedwith fluid buildup.

Embodiments of the present invention that are described hereinbelowprovide such diagnostic monitoring functions by means of an implantabledielectrometric device. The device comprises a sealed case, comprising abiocompatible material, which is implanted in the body of a humansubject. The case is connected to or contains a dielectrometric probe,comprising a pair of conductors, which are placed in proximity to atarget tissue, such as the lung. The term “proximity,” in the context ofthe present patent application and in the claims, means that the targettissue is close enough to the distal end of the probe to have asignificant impact on the impedance between the conductors. “Proximity”in the context of the embodiments described below is generally limitedto a distance of not more than 1-2 cm from the target tissue.

A driving circuit in the sealed case applies a radio-frequency (RF)signal to the probe and senses the signal returned from the probe inorder to measure the impedance between the conductors. This impedancewill vary as a function of the dielectric properties of the targettissue, including the permittivity and conductivity, which togetherdefine the complex permittivity of the tissue. The driving circuittypically applies the RF signal to the probe at multiple differentfrequencies, so that the complex permittivity is measured as a functionof frequency. A processing circuit may then evaluate the dielectricproperties of the target tissue based on the measured impedance.Following the impedance calculation over frequency, a water contentassumption can be estimated based on multi-material liquid model withthe respective permittivity over different frequencies.

In a general material including loss and permittivity, impedance isdefined as follows:

$\begin{matrix}{\eta = \frac{j\omega\mu}{\gamma}} & (1)\end{matrix}$Here ω is the radial frequency, and μ is the material permeability(which in the case of a biological tissue is equal to the free spacepermeability μ=μ₀). γ is the complex propagation constant which isdefined as follows:

$\begin{matrix}{\gamma = {{j\omega}\sqrt{\mu\; ɛ_{0}}\sqrt{ɛ^{\prime} - {j\; ɛ^{''}}}}} & (2)\end{matrix}$

In this equation, c₀ is the free-space electromagnetic propagationvelocity, and ∈′ and ∈″ are the real and imaginary part of the complexpermittivity. As noted earlier, the imaginary part of the complexpermittivity is related to the conductivity:∈″=σ/ω∈₀.  (3)The above expressions are thus used to relate the measured impedance, asa function of frequency, to the complex permittivity.

The impedance between the conductors due to the target tissue can bemeasured in a number of ways. In some embodiments, the driving circuitmeasures the reflection of the signal from the probe, which isindicative of an impedance mismatch at the target tissue at the end ofthe probe. In other embodiments, the driving circuit measures the delayof the signal transmitted through the probe, which is indicative of thepermittivity of the target tissue. In other embodiments, the drivingcircuit measures a resonating frequency of a printed resonator (such asa ring or other shaped circuit), which is indicative of the propertiesof tissues in its proximity. Various probe configurations that may beused for these types of measurements are described hereinbelow.

The embodiments that are shown in the figures and are described beloware directed to devices that are implanted in the thorax for purposes ofmonitoring fluid levels in the lungs. Alternatively, the principles ofthe present invention may similarly be applied in other monitoringapplications. For example, implanted devices of the types describedherein may be used, mutatis mutandis, in monitoring pericardial fluidlevels. In other embodiments, such devices may be used in long-termmonitoring of fluid levels in the brain, spleen, tongue, palate orliver, as well as in body extremities, such as the thighs. Moregenerally, the devices and methods described herein may be adapted foruse in substantially any long-term diagnostic application in whichmeasuring the dielectric properties of tissue is of value, including notonly fluid monitoring but also imaging applications, as well.

System Description and Probe Configurations

FIG. 1 is a schematic pictorial illustration showing a monitoring system20 including a dielectrometric monitoring device 24 implanted in thethorax of a patient 22, in accordance with an embodiment of theinvention. Device 24 comprises an electronic unit 28, which is typicallysimilar in shape and size to a conventional implanted cardiac device(ICD), such as a pacemaker, and is implanted below the patient's skinusing a minimally-invasive procedure. (In an alternative embodiment,device 24 may also include electrodes and be configured to pace thepatient's heart, in addition to the diagnostic functions that aredescribed herein.) Device 24 may alternatively be implanted in otherlocations, as shown in FIGS. 8 and 9, for example.

Electronic unit 28 is connected to a probe 26 by a cable 30. Probe 26 ispositioned in or alongside a lung 34 of patient 22. Device 24 drives theprobe via the cable with RF signals, typically including multiplesignals at different frequencies within a chosen range, such as themicrowave range. Optionally, the frequency range may be even wider, from100 MHz to 2.5 GHz, for example, or even from a few kHz up to severalGHz, depending on the desired resolution, depth and permittivity rangeof the measurements. The circuits in unit 28 measure the impedance ofthe probe in response to the signals, which depends on the dielectricproperties (permittivity and conductivity) of the lung tissue that is inproximity to the probe.

Based on the measured impedance, device 24 derives an indication of thedielectric properties of the tissue in lung 34. These dielectricproperties are themselves indicative of physiological conditions of thetissue, such as fluid content. Device 24 collects these indications overtime and periodically transmits the data to a telemetry station 32,typically via a suitable short-range wireless link. Alternatively oradditionally, device 24 may transmit the raw impedance measurements tostation 32, which then processes the measurements itself to extract thedielectric properties and physiological conditions of the tissue.

Station 32 typically comprises a general-purpose computer with suitablecommunication circuits and software, and may be located in a clinic orhospital or in the home or workplace of patient 22. Station 32 may alsobe configured to program device 24 over the wireless link, as well as toprovide RF energy to recharge the battery in device 24, as describedbelow. Station 32 may also comprise a gateway, relaying informationbetween device 24 and a server across a network, as well as serving asthe user interface for the device. Such a gateway may be, for example, adesktop station or a smart-phone.

FIG. 2 is a schematic pictorial view of dielectrometric probe 26, inaccordance with an embodiment of the invention. Cable 30 comprises apair of conductors 46, 48, arranged coaxially. The conductors terminatein this embodiment in an open-coax patch arrangement, in which conductor46 connects to a central electrode 40, and conductor 48 connects to aring electrode 42 surrounding electrode 40. Electrodes 40 and 42 areseparated by a non-conductive ring 44. Probe 26 may comprise, forexample, a flexible or rigid circuit substrate (not shown), made from abiocompatible material, on which electrodes 40 and 42 are printed orotherwise deposited. Although probe 26 is shown in this figure as beingoriented perpendicular to coaxial cable 30, in other embodiments, theprobe may be oriented parallel to the cable.

The impedance between conductors 46 and 48 within cable 30 is fixed, butthe impedance between electrodes 40 and 42 at the termination of theconductors will vary as a function of the complex permittivity of thetissue in proximity to probe 26. RF signals transmitted down cable 30 toprobe 26 will be reflected back from the probe due to the mismatchbetween the cable impedance and the impedance encountered by the probedue to the tissue permittivity. The amplitude and phase of the reflectedsignal at any given frequency will depend on the impedance encounteredby the probe at that frequency. Device 24 analyzes the amplitude andphase of the reflected signals over a range of frequencies in order toderive a measure of the complex impedance.

FIG. 3 is a schematic pictorial view of a dielectrometric probe 50, inaccordance with another embodiment of the invention. Probe 50 may beused with device 24 in place of probe 26 in the system configurationthat is shown in FIG. 1. Alternatively, probe 50 may be mounted directlyon the electronic unit of a dielectrometric device, which is thenimplanted itself in proximity to the target tissue. In this latteralternative embodiment (not shown in the figures), cable 30 is notneeded.

In the embodiment of FIG. 3, probe 50 is configured as a microstriptransmission line. One of the conductors in cable 30 connects to aground plane 56 on one side of a circuit substrate 52. The otherconductor connects to a microstrip 54 on the opposite side of substrate52. The complex permittivity of the tissue in proximity to microstrip 54changes the effective permittivity of the transmission line at its crosssection, thus changing its characteristic impedance and velocity factor.These impedance and velocity factors affect both the amplitude and thepropagation delay of the signals passing through the transmission linein probe 50 and cable 30. Either or both of these properties may bemeasured in order to assess the impedance and thus estimate thepermittivity of the target tissue. To measure the propagation delay,both ends of microstrip 54 may be connected by conductors to the drivercircuits in device 24, rather than only one end as in the picturedembodiment.

FIG. 4A is a schematic sectional view of probe 50, showing lines of theelectric field emitted from the probe, in accordance with an embodimentof the invention. Although this figure shows a particular stripline-typetransmission line configuration, the principles of this embodiment applyequally to other sorts of transmission lines, such as a coplanarwaveguide, grounded coplanar waveguide, parallel lines, as shown in thefigures that follow, or any other transmission line configuration.

The lines of field emitted from microstrip 54 in FIG. 4A pass throughintermediate tissue 58, with which probe 50 is in contact (such as thepleura), into target tissue 62 (such as the lung). Changes in thedielectric properties of target tissue 62 will affect the field linesand consequently the impedance of the transmission line. Thecross-sectional configuration of probe 50 is optimized to achieve widespreading of the electric and magnetic fields, in order to increase thesensitivity of the probe to dielectric changes in tissue 62. Generallyspeaking, the configuration is chosen so that the electromagnetic fluxis denser at the deeper targeted measurement volume. The probe is thusable to sense dielectric change at larger distances. For measuring lungfluid content, probe 50 is typically 1-2 cm wide and a few millimetersthick.

FIGS. 4B and 4C are schematic pictorial views of dielectrometric probes63 and 66, in accordance with alternative embodiments of the presentinvention. Probe 63 comprises two parallel conducting lines 64 formed onone side of a substrate, with a ground plane 65 formed on the other.Probe 66 is a grounded coplanar waveguide, with a conductive strip 67between coplanar ground planes 68 on one side of a substrate and aground plane 69 on the other.

Elimination of ground plane 69 would make probe 66 a simple coplanarwaveguide. FIG. 5 is a schematic side view of a dielectrometric probe70, in accordance with yet another embodiment of the invention. Probe 70may also be used with device 24 in place of probe 26 in system 20. Probe70 comprises a coaxial tip at the end of cable 30, in which a centralconductor 72 is concentrically contained within a peripheral conductivecylinder 74. Central conductor 72 protrudes from surrounding cylinder 74and can even be inserted into the target tissue. This geometry enablesimpedance measurement deeper into the tissue. Contact between the tipand the tissue causes an impedance mismatch with cable 30, leading toreflections that can be used to measure complex permittivity as in thepreceding embodiments.

Signal Processing

FIG. 6 is a block diagram that schematically shows functional componentsof dielectrometric monitoring device 24, in accordance with anembodiment of the invention. The elements of electronic unit 28 arecontained in a sealed case 80 comprising a suitable biocompatiblematerial, such as titanium or stainless steel. Case 80 contains, interalia, circuitry including a front end driver circuit 82 and a digitalprocessing circuit 84. Driver circuit 82 comprises a transmitter 94,which transmits RF signals via a directional coupler 95 or bridgethrough cable 30 to probe 26 (or to one of the other probes describedabove). A receiver 96 in the driver circuit receives the signals thatare returned from probe 26 via cable 30 and outputs a digitizedindication of the amplitude and phase of the signals to digitalprocessing circuit 84. Typically, the driver circuit applies the signalsat multiple, different frequencies, and uses frequency-tuned detectionin sensing the returned signal at each frequency.

Processing circuit 84 samples the input signals transmitted by drivercircuit 82, and uses the sampled input as an amplitude and phasereference. The processing circuit then compares the digitized signalsreceived from the driver circuit to the reference in order to calculatethe amplitude and phase shift of the returned signals. Based on theamplitude and phase shifts and/or the propagation delay of the receivedsignal relative to the transmitted signal, taken as a function offrequency over the range of frequencies transmitted by the drivercircuit, processing circuit 84 derives the complex impedance between theconductors of the probe due to the target tissue. The processing circuit(or station 32, FIG. 1) evaluates the permittivity of the target tissuebased on these measurements.

The circuits of device 24 measure the permittivity in order to computean indication of the fluid content of lung 34. These measurements may bemade continuously, or they may be made periodically and/or on command.Typically, digital processing circuit 84 comprises a memory (not shown),which stores the computed values. Circuit 84 may perform statisticalanalyses on the recorded values over time, such as computing trends andchanges. Circuit 84 may issue an alarm if the fluid content rises abovea predetermined threshold level.

To determine the permittivity, processing circuit 84 may transform thefrequency-domain measurements of the returned signals to the timedomain, filter the time-domain signals to remove spurious reflectionsdue to impedance discontinuities along the line to probe 26, and thentransform the filtered signals back to the frequency domain. Circuit 84may derive the load admittance Ymeas of the probe from the measuredsignals using the following formula:

$\begin{matrix}{{Y\;{meas}} = {{\sigma + {j\; B}} = {Y_{0}\frac{1 - {\Gamma\;{meas}}}{1 + {\Gamma\;{meas}}}}}} & (4)\end{matrix}$Here Γmeas is the measured reflection coefficient in the frequencydomain, and Yo is the characteristic admittance of the transmissionline. The load admittance is composed of a parallel conductance σ and asusceptance B. The susceptance reflects the edge capacitance of theprobe, which in turn is related to the permittivity of the tissue.

Incorporating the capacitance and conductance functions into equation(4) and matching with the measured admittance gives the expression:Ymeas/Y ₀ =jωC ₁ Z ₀ +jω′∈Z ₀ +Z ₀σ  (5)wherein Z₀ is the characteristic impedance of the measurementtransmission line. A non-linear solver can be applied to the admittancevalues given in equation (4) to extract the conductance and capacitanceof the tissue. The complex permittivity is the found using equations(1)-(3) above. The real permittivity is related to ∈₂, while theimaginary permittivity is related to both the frequency and theconductivity.

The water content of the tissue may be derived from the measuredpermittivity using empirical calibration curves or other techniques thatare known in the art. Techniques that may be used for this purpose aredescribed, for example, by Miura et al., in “Time Domain Reflectometry:Measurement of Free Water in Normal Lung and Pulmonary Edema,” AmericanJournal of Physiology—Lung Physiology 276:1 (1999), pages L207-L212,which is incorporated herein by reference.

Device 24 may optionally comprise additional sensors 97, connected toelectronic unit 28. Sensors 97 may comprise, for example, one or moreelectrodes, which sense electrical activity of the heart. The resultingsignals can be used to gate the measurements of dielectric properties ofthe tissue. Additionally or alternatively, sensors 97 may comprise aposture or motion sensor, such as an accelerometer. Posture inparticular has an effect on fluid distribution within the lungs, andprocessing circuit 84 may use the posture measurement in refining itsassessment of fluid content. Further additionally or alternatively,processing circuit may detect a modulation of the dielectric propertiesdue to the heartbeat and/or respiratory motion of the subject.

A communication interface 86 transmits and receives data to and fromtelemetry station 32 (FIG. 1) via a communication antenna 88. Thetransmitted data typically comprise the indications of permittivityand/or tissue fluid content that have been computed over time and storedby digital processing circuit 84. Alternatively or additionally, circuit84 may transmit raw data regarding the returned signals and/or impedancefor further processing in the telemetry station. Further alternativelyor additionally, communication interface 86 may transmit datacontinuously as they are measured.

A power source 90 supplies operating power to the circuits of device 24.Power source 90 typically comprises an energy storage component, such asa single-use or rechargeable battery. In the case of a rechargeablestorage component, power source 90 may be coupled to a power antenna 92,which receives RF power from a suitable power transmission antenna (notshown) outside the body. Such a transmission antenna may comprise, forexample, a coil, which is positioned outside the body of patient 22 inproximity to device 24 and provides power to antenna 92 by magneticinduction. The power transmission coil may be placed under a mattress onwhich the patient lies, or it may be worn as a vest, a bra or anecklace, for example. Power source 90 rectifies the received power inorder to charge its energy storage component.

FIG. 7A is a plot showing the relationship between tissue permittivityand signal delay measured by dielectrometric monitoring device 24, inaccordance with an embodiment of the invention. This plot is based on asimulation of the performance of a transmission line-type probe, such asprobe 50 (FIGS. 3-4). The permittivity of the tissue in the simulationis varied between 20 and 50, and the delay through the line iscalculated and normalized in terms of nanoseconds per meter of length.There is a clear linear relation between the measured phase and theevaluated permittivity.

The delay thus provides a reliable measure of tissue permittivity. Inaddition, as the permittivity changes, there will also be an amplitudechange in the returned signals due to impedance mismatch and ohmiclosses. Each probe used in system 20 may be pre-calibrated in order tofind the exact relation between delay and/or amplitude of the returnedwave and the tissue permittivity, and the resulting calibration factorsmay then be programmed into processing circuit 84.

FIG. 7B is a plot of the complex permittivity of lung tissue as afunction of frequency, in accordance with an embodiment of the presentinvention. The real and imaginary parts of the permittivity are shown byrespective curves 98 and 99. These permittivity values were derived fromexperimental results using the relations expressed by equations (4) and(5) above.

Alternative Implant Locations and Implantation Techniques

FIG. 8 is a schematic, sectional view through the thorax of a humansubject, showing implantation of a dielectrometric monitoring device 100in the thorax, in accordance with an embodiment of the invention. Toimplant device 100, the surgeon makes a small incision through skin 106and through muscle 110 between ribs 108. A probe 102 is then threaded,through the incision, into the rib cage, so that the probe is positionedoutside pleura 104 of lung 34, and an electronics unit 112 is connectedto the probe. Typically, unit 112 is placed between two of the lowerribs at the side of the thorax. Tissue-growth inducing materials 114 maybe applied around unit 112 in order to facilitate tissue integration ofthe device. Electronic unit 112 and a thin, circular coil 116 are leftoutside ribs 108. Coil 116 enables charging of device 100, as describedabove. Unit 112 is attached to the ribs using standard attachmentmethods.

FIG. 9 is a schematic, sectional view through the thorax of a humansubject, showing implantation of a dielectrometric monitoring device 120in the thorax, in accordance with another embodiment of the invention.In this case, an electronic unit 122 of device 120 is made small enoughto allow internal placement, inside the rib cage.

FIG. 10 is a schematic pictorial illustration of a surgical tool 130 foruse in implantation of dielectrometric probe 102, in accordance with anembodiment of the present invention. Tool 130 comprises a receptacle 132at its distal end, into which end terminals 134 of probe 102 areinserted. (After probe 102 has been implanted and properly positionedusing tool 130, receptacle 132 is disengaged from terminals 134, whichare then connected to electronics unit 112.) For ease of implantation,probe 102 may be internally reinforced so as to bend freely in only onedirection (the downward direction in FIG. 10), while resisting bendingin any other direction.

Tool 130 comprises an optical channel 136, such as a fiberoptic bundle,which runs along the upper surface of probe 102 when the probe isconnected to receptacle 132. Channel 136 connects to an image sensor anda light source (not shown in the figures) inside tool 130, which in turnconnect via a cable 138 to a console (not shown). The surgeon implantingprobe 102 is thus able to view the area between and behind ribs 108during implantation. A navigation knob 140 enables the surgeon to movechannel 136 up and down, and possibly to move probe 102 along with it. Afluid connection allows water to be introduced to rinse channel 136.

FIG. 11 is a schematic pictorial illustration showing a surgicalaccessory 150 for use in implantation of probe 102, in accordance withan embodiment of the present invention. The surgeon inserts a distal tip152 of accessory 150 between ribs 108, thus defining an entry path forprobe 102 (with or without the use of tool 130). A stopper 154 limitsthe depth of insertion of tip 152 and thus prevents unnecessary traumato the patient. After inserting accessory 150 between the ribs, thesurgeon threads the distal end of probe 102 through an opening 156, andtip 152 then guides the distal end downward to the desired positionadjacent to pleura 104. The accessory is then removed, and probe 102 isaffixed to its location, for example by sewing it to the rib or muscleor connective tissue surrounding the ribs.

Resonant Probe

FIG. 12 is a schematic top view of a dielectrometric probe 160, inaccordance with a further embodiment of the present invention. Probe 160comprises a conductive ring 162, which is printed on a substrate 166.Conductors 164 on substrate 166 link ring 162 to ports 168, with smallgaps between the conductors and the ring to isolate the ring for thepurpose of resonance measurements.

When ring 162 is excited by an electromagnetic wave transmitted betweenports 168, a standing wave is created in the ring. The points of maximumand minimum voltage in the standing wave depend on the propagationvelocity in the ring, which in turn depends on the permittivity of thetissue in proximity to the ring. The ring will have a number of resonantfrequencies (in first- and higher-order modes), which depend on thetissue permittivity. The size and other parameters of ring 162 arechosen so that the resonant frequencies depend on the permittivity at aparticular depth within the tissue. The excitation frequency of probe160 is scanned over a range of frequencies in order to find the resonantfrequency of ring 162 and thus measure the tissue permittivity.

FIG. 13 is a plot showing the frequency response of probe 160 fordifferent values of the tissue permittivity, in accordance with anembodiment of the present invention. The vertical axis of the plotcorresponds to the reflection coefficient of the probe, which drops by3-5 dB at the resonant frequency. Curves 172, 174, 176 and 178 show thecoefficient as a function of frequency for tissue permittivity values of20, 30, 40 and 50, respectively. The resonance frequency shifts over arange of about 500 MHz. By measuring this frequency shift, probe 160thus provides an accurate measure of the tissue permittivity, and henceof the fluid level.

In an alternative embodiment (not shown in the figures), adielectrometric probe is placed near the diaphragm and has sensingflaps, which make it possible to measure not only lung fluids, but alsoliver fluids (to the right) or spleen fluids (to the left). Thedielectrometric device and probe can be designed to permit multipledifferent measurements of this sort to be made, even simultaneously.Although the embodiments shown in the figures relate specifically tomeasurement of the fluid content of the lungs, the principles of thepresent invention may similarly be applied in monitoring of otherorgans, such as the heart, bladder, spleen, liver, tongue, palate,brain, and body extremities.

It will thus be appreciated that the embodiments described above arecited by way of example, and that the present invention is not limitedto what has been particularly shown and described hereinabove. Rather,the scope of the present invention includes both combinations andsubcombinations of the various features described hereinabove, as wellas variations and modifications thereof which would occur to personsskilled in the art upon reading the foregoing description and which arenot disclosed in the prior art.

The invention claimed is:
 1. A diagnostic method, comprising: implantinga dielectrometer probe, comprising first and second conductors, inproximity to a target tissue in a body of a human subject; applying aradio-frequency (RF) signal to the probe; and evaluating, responsivelyto a signal from the probe, a dielectric property of the target tissueincluding finding a complex permittivity of the target tissue, whereinfinding the complex permittivity of the target tissue includes one of:measuring a reflection of the signal from the probe, which is indicativeof an impedance mismatch at the target tissue; measuring a delay of thesignal transmitted through the probe; and measuring a resonant frequencyof the probe.
 2. The method according to claim 1, wherein applying theRF signal comprises applying RF signals and sensing returned signals atmultiple different frequencies.
 3. The method according to claim 1,wherein finding the complex permittivity further includes measuring animpedance between the first and second conductors.
 4. A diagnosticmethod, comprising: implanting a dielectrometer probe, comprising firstand second conductors, in proximity to a target tissue in a body of ahuman subject; applying a radio-frequency (RF) signal to the probe; andevaluating, responsively to a signal from the probe, a dielectricproperty of the target tissue; wherein the first and second conductorsare arranged to: provide a coaxial contact to the target tissue at adistal end of the probe, or define a resonant ring in proximity to thetarget tissue.
 5. The method according to claim 4, wherein the first andsecond conductors are arranged to provide a coaxial contact to thetarget tissue at a distal end of the probe, and the coaxial contactcomprises a patch, which is placed against the target tissue.
 6. Themethod according to claim 4, wherein the first and second conductors arearranged to provide a coaxial contact to the target tissue at a distalend of the probe, and the coaxial contact comprises a coaxial tip, inwhich the first conductor is concentrically contained within the secondconductor, wherein the tip is inserted into the target tissue.
 7. Adiagnostic method, comprising: implanting a dielectrometer probe,comprising first and second conductors, in proximity to a target tissuein a body of a human subject; the first and second conductors arrangedto define a transmission line in proximity to the target tissue;applying a radio-frequency (RF) signal to the probe; and evaluating,responsively to a signal from the probe, a dielectric property of thetarget tissue; wherein: the transmission line is defined by arrangingthe first conductor as a ground plane and the second conductor as amicrostrip parallel to the ground plane; or the transmission linecomprises a coplanar waveguide.
 8. The method according to claim 4,wherein the first and second conductors are arranged to define atransmission line in proximity to the target tissue and the transmissionline is defined by arranging the first and second conductors as parallellines.
 9. The method according to claim 1, further comprising deriving ameasure of a fluid content of the target tissue from the dielectricproperty.
 10. The method according to claim 9, wherein deriving themeasure comprises measuring the fluid content continuously.
 11. Themethod according to claim 9, wherein deriving the measure comprisesmeasuring the fluid content intermittently.
 12. The method according toclaim 9, wherein deriving the measure comprises measuring changes in thefluid content over time.
 13. The method according to claim 1, furthercomprising implanting a case, which is connected to the probe, in athorax of the subject.
 14. The method according to claim 4, furthercomprising deriving a measure of a fluid content of the target tissuefrom the dielectric property.
 15. The method according to claim 14,wherein deriving the measure comprises measuring changes in the fluidcontent over time.
 16. The method according to claim 4, wherein applyingthe RF signal comprises applying RF signals and sensing returned signalsat multiple different frequencies.
 17. The method according to claim 7,further comprising deriving a measure of a fluid content of the targettissue from the dielectric property.
 18. The method according to claim14, wherein deriving the measure comprises measuring changes in thefluid content over time.
 19. The method according to claim 7, whereinapplying the RF signal comprises applying RF signals and sensingreturned signals at multiple different frequencies.